EP3178417A1 - Minimally invasive bone sparing acetabular reamer - Google Patents
Minimally invasive bone sparing acetabular reamer Download PDFInfo
- Publication number
- EP3178417A1 EP3178417A1 EP16203474.8A EP16203474A EP3178417A1 EP 3178417 A1 EP3178417 A1 EP 3178417A1 EP 16203474 A EP16203474 A EP 16203474A EP 3178417 A1 EP3178417 A1 EP 3178417A1
- Authority
- EP
- European Patent Office
- Prior art keywords
- insert
- collar
- shell
- sidewall
- bone cutter
- Prior art date
- Legal status (The legal status is an assumption and is not a legal conclusion. Google has not performed a legal analysis and makes no representation as to the accuracy of the status listed.)
- Granted
Links
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- 210000001519 tissue Anatomy 0.000 claims abstract description 58
- 230000000399 orthopedic effect Effects 0.000 claims abstract description 53
- 230000036346 tooth eruption Effects 0.000 claims abstract description 24
- 210000000588 acetabulum Anatomy 0.000 description 26
- 238000000034 method Methods 0.000 description 8
- 238000003780 insertion Methods 0.000 description 6
- 230000037431 insertion Effects 0.000 description 6
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- 239000000853 adhesive Substances 0.000 description 2
- 230000001070 adhesive effect Effects 0.000 description 2
- 238000011882 arthroplasty Methods 0.000 description 2
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Images
Classifications
-
- A—HUMAN NECESSITIES
- A61—MEDICAL OR VETERINARY SCIENCE; HYGIENE
- A61B—DIAGNOSIS; SURGERY; IDENTIFICATION
- A61B17/00—Surgical instruments, devices or methods, e.g. tourniquets
- A61B17/16—Bone cutting, breaking or removal means other than saws, e.g. Osteoclasts; Drills or chisels for bones; Trepans
- A61B17/1662—Bone cutting, breaking or removal means other than saws, e.g. Osteoclasts; Drills or chisels for bones; Trepans for particular parts of the body
- A61B17/1664—Bone cutting, breaking or removal means other than saws, e.g. Osteoclasts; Drills or chisels for bones; Trepans for particular parts of the body for the hip
- A61B17/1666—Bone cutting, breaking or removal means other than saws, e.g. Osteoclasts; Drills or chisels for bones; Trepans for particular parts of the body for the hip for the acetabulum
-
- A—HUMAN NECESSITIES
- A61—MEDICAL OR VETERINARY SCIENCE; HYGIENE
- A61B—DIAGNOSIS; SURGERY; IDENTIFICATION
- A61B17/00—Surgical instruments, devices or methods, e.g. tourniquets
- A61B17/16—Bone cutting, breaking or removal means other than saws, e.g. Osteoclasts; Drills or chisels for bones; Trepans
- A61B17/1659—Surgical rasps, files, planes, or scrapers
-
- A—HUMAN NECESSITIES
- A61—MEDICAL OR VETERINARY SCIENCE; HYGIENE
- A61B—DIAGNOSIS; SURGERY; IDENTIFICATION
- A61B17/00—Surgical instruments, devices or methods, e.g. tourniquets
- A61B17/16—Bone cutting, breaking or removal means other than saws, e.g. Osteoclasts; Drills or chisels for bones; Trepans
- A61B17/1613—Component parts
- A61B17/1615—Drill bits, i.e. rotating tools extending from a handpiece to contact the worked material
- A61B17/1617—Drill bits, i.e. rotating tools extending from a handpiece to contact the worked material with mobile or detachable parts
-
- A—HUMAN NECESSITIES
- A61—MEDICAL OR VETERINARY SCIENCE; HYGIENE
- A61B—DIAGNOSIS; SURGERY; IDENTIFICATION
- A61B17/00—Surgical instruments, devices or methods, e.g. tourniquets
- A61B17/16—Bone cutting, breaking or removal means other than saws, e.g. Osteoclasts; Drills or chisels for bones; Trepans
- A61B2017/1602—Mills
Definitions
- the present invention relates to the art of orthopedic cutting devices, more particularly, to an orthopedic cutting device designed to remove bone and tissue from the acetabulum.
- Reamers are devices intended to remove tissue and bone from the human body. Similarly to that of a traditional reamer device, the orthopedic cutting device of the present invention is designed to remove bone and tissue from the cotyloid cavity or acetabulum in preparation for the insertion of a prosthetic cup during hip arthroplasty.
- the cotyloid cavity is a cup shaped cavity at the base of the hipbone into which the ball-shaped head of the femur is received ( FIG. 15 ).
- the acetabulum comprises an acetabulum bone floor that extends to the acetabular roof, the bone structure that resides along the upper portion of the cotyloid cavity.
- the acetabular fossa a depressed area having a relatively thin bone structure, resides about the center of the acetabular floor.
- the acetabular labrum, a ring of fibrous cartilage, resides along the outer perimeter of the cotyloid cavity.
- acetabular reamers such as the one disclosed in U.S. Pat. No. 5,709,688 to Salyer, are generally constructed having a rigid hemispherical shell structure with a continuous hemispherical surface. A plurality of spaced apart teeth, arranged in the same direction, outwardly extend from the shell exterior. The hemispherical structure is suited to create a cavity within the acetabulum which receives a prosthetic cup. Prosthetic cups generally have a curved exterior surface that is inserted into the cotyloid cavity.
- a series of prior art reamers are used to form a hemispherically shaped cavity within the acetabulum.
- the series of prior art reamers of increasing diameter are typically used to gradually form a hemispherical cavity, reaming from the acetabular floor and fossa outwards to the acetabular labrum until a desired diameter is reached.
- Prior art orthopedic reamers are typically fabricated as modular units that are sold in a set of an array of diameters. These reamer tool sets are generally manufactured with reamer cutting heads providing bore sizes ranging from about 36 mm to about 80 mm in 1 mm increments sometimes totaling over 45 sizes. Since it is desirable to achieve a close prosthetic fit, a wide array of reaming tools of varying sizes are required to be on hand to provide the most precise cut and optimum bore diameter.
- the rigid hemispherical shape of prior art reamers causes the hemispherical cavity to gradually be formed of increasing diameter from the acetabular fossa at the center of the acetabular floor outwards to the acetabular roof.
- the reamer apex contacts and abrades the acetabular floor and fossa.
- Such a procedure is believed to remove excessive bone from the acetabular fossa, thus resulting in a reamed acetabulum having reduced strength and rigidity.
- the insertion and removal of multiple prior art reamers may potentially lead to infection.
- the procedure of inserting and removing multiple prior art reamers is potentially traumatic to the body.
- the present invention addresses these potential problems by providing a bone cutter that is configured to ream the cotyloid cavity with one device.
- the bone cutter of the present invention is designed to ream the acetabular roof and acetabular labrum prior to significantly reaming the acetabular floor and acetabular fossa. Therefore, abrasion to the acetabular floor and fossa is reduced, thus resulting in the preservation of more of the acetabular floor and fossa bone structure.
- the bone structure of the reamed acetabulum has greater strength and rigidity in comparison to an acetabulum that is reamed by the prior art procedure with the prior art reamers.
- the bone cutter of the present invention eliminates the need to introduce and remove multiple prior art reamers, the risk of infection and trauma is minimized.
- the acetabular reamer of White comprises a fixed rigid reamer shell that necessitates the use of multiple reamer devices to create a hemispherical cavity of a desired diameter.
- the rigid partial hemispherical design may cause additional abrasion of the acetabular fossa and floor as the apex of the multitude of increasingly large reamers come into contact with the acetabular floor surface.
- Ezzedine discloses a collapsible surgical reamer having a hinge along its rotating axis. While the collapsed configuration allows for the device to pass through a minimally invasive incision, the Ezzedine device must be in an unfolded configuration to ream bone and tissue.
- the Ezzedine reamer comprises a rigid hemispherical shape having teeth that extend from the hemispherical structure when used within the body.
- the rigid hemispherical structure of the Ezzedine reamer may cause additional abrasion to the acetabular floor and fossa during a procedure which may potentially cause the acetabulum to become less rigid.
- Sherry et al. in U.S. Pat. No. 8,052,689 , which is assigned to the assignee of the present invention and incorporated herein by reference.
- Sherry discloses an acetabular reamer having a truncated cutting shell that is constructed without an apex. The omission of the apex from the reamer shell allows for the reaming of the acetabular roof and acetabular labrum without contacting the acetabular fossa.
- the Sherry device in order to form a full hemispherical cavity within the acetabulum, the Sherry device must be rocked in a back and forth manner for the cutting teeth to contact the acetabular floor region. Such a rocking motion is not preferred as this may not produce a true hemispherical cavity. Furthermore, the rocking motion of the reamer within the body may aggravate and traumatize surrounding tissue.
- the '689 to Sherry et al. patent discloses an alternate embodiment comprising a cap or plate that is positioned over the apex opening. As disclosed by Sherry, the cap or plate is stationary, but separately attached to the shell. Thus, in order to attach the cap or plate, the shell must either be removed from the body or manipulated by the surgeon within the body. In either case, the removal and insertion or the manipulation of the shell within the body to attach the apex cap may cause additional trauma or result in infection to the patient.
- the bone cutter of the present invention comprises a bone cutting insert that extends and retracts from within an opening that extends through the reamer shell.
- the bone cutter of the present invention is configured such that the insert is capable of rotational and axial movement independent of the reamer shell.
- the bone cutter when the insert is retracted within the reamer shell, the bone cutter is configured to ream the acetabular labrum and roof. The acetabular fossa or floor may then be reamed by outwardly extending the insert from within the reamer shell without removing the bone cutter from the body.
- the retracted configuration of the bone cutter of the present invention provides for insertion within a minimally invasive incision.
- the present invention provides a reamer that incorporates design features which address various limitations of the prior art.
- the features of the bone cutter of the present invention enable the reaming of the acetabular roof and the acetabular floor in separate steps without removal of the device from the body, thus more of the bone structure of the acetabulum preserved while minimizing patient trauma and infection.
- the present invention is an orthopedic cutting device designed to cut and remove tissue and bone material.
- the device is designed to efficiently remove tissue and bone from the cotyloid cavity for the insertion of an orthopedic implant.
- the bone cutter comprises a reamer shell and a reamer insert that resides within an opening that extends through the apex of the reamer shell.
- the insert is capable of independent axial and rotational movement within the shell opening.
- the reamer shell is preferably of a partially hemispherical structure comprising a plurality of spaced apart shell teeth, each having a tissue cutting surface that extends outwardly from the reamer shell exterior surface.
- the insert preferably comprises an annular sidewall that meets an insert end wall that comprises a plurality of spaced apart insert cutting teeth having a tissue cutting surface.
- the insert rides within a pin and slot mechanism that is positioned within the shell interior. This pin and slot mechanism provides axial and rotational movement of the insert with respect to the shell.
- the insert is positioned within a collar that is secured within the reamer interior.
- the collar comprises an annular sidewall having a slot extending to a groove formed at least partially within the collar sidewall interior surface. A pin extending from the insert sidewall is received within the collar slot and rides therewithin.
- the insert is positioned within a collar that is secured within the reamer interior.
- the collar comprising an annular sidewall having at least one pin that extends outwardly from the collar sidewall interior surface.
- the insert comprising an insert sidewall having a slot extending to a groove is formed at least partially within the insert sidewall exterior surface. The pin extending from the collar sidewall interior surface is received within the insert slot and rides therewithin.
- the bone cutter When the insert is in a retracted position the bone cutter is configured to ream the acetabular roof. In addition, the retracted configuration provides a low profile orientation that helps allow for the insertion of the reamer through a minimally invasive incision. When the insert is in an extended position, the bone cutter is configured to ream the acetabular floor.
- the bone cutter of the present invention provides for the separate reaming of the acetabular roof and floor without the need to remove the device from the body.
- FIGS. 1 to 3 , 4A , 4B , and 5 illustrate an embodiment of a bone cutter 10 of the present invention.
- the bone cutter 10 extends from a bone cutter base 12 at a proximal end 14 to an apex 16 at a distal end 18.
- An imaginary rotational axis A-A extends through the apex 16.
- the bone cutter 10 comprises a reamer shell 20, and a reamer insert 22. Both the reamer shell 20 and insert 22 are configured to cut bone and tissue.
- the reamer insert 22 is positioned within an opening 24 ( FIG. 6 ) that extends through a thickness of the shell 20 adjacent to the apex 16.
- the insert 22 is designed to rotate either in a clockwise or counter-clockwise direction independent of the reamer shell 20 within the opening 24.
- the insert 22 is configured to move in an axial direction along the rotational axis A-A within the shell opening 24.
- the shell 20 is configured to ream the acetabular roof and labrum while the movable bone cutting insert 22 enables independent reaming of the acetabular floor and fossa.
- the bone cutter 10 of the present invention thus eliminates the need to remove and insert multiple reamers of increasing diameter during a procedure. Therefore, the possibility that surgical trauma or infection may result is minimized.
- the insert 22 may be positioned below the shell opening 24 within the shell interior thus providing the bone cutter 10 of the present invention with a low profile that is minimally invasive to insert and remove from the body.
- the retractable reamer insert 22 allows for the reaming of the acetabular roof 28 and acetabular labrum 30 prior to the reaming of the acetabular fossa 32 which resides within the acetabular floor.
- the hip resurfacing handbook A practical guide to the use and management of modern hip resurfacings, 2013 , reaming the acetabular labrum 28 prior to the acetabular fossa 30 during a hip replacement surgical procedure is beneficial as it preserves more of the acetabulum bone structure.
- FIG. 6 illustrates an embodiment of the reamer shell 20.
- the reamer shell 20 comprises a sidewall 34 having a curvature comprising a partial hemispherical shape that extends from a shell base 36 having a base edge 38, that defines a shell base perimeter at a shell proximal end 40.
- the sidewall 34 extends from the base 36 towards an intermediate edge that defines an intermediate perimeter at a shell distal end 42.
- the intermediate perimeter is located on an imaginary intermediate plane that is spaced from and positioned between the imaginary apex 16 and the base edge 38.
- the intermediate perimeter defines the opening 24 having a region 44 that radially extends from the imaginary rotational axis A-A at the bone cutter apex 16.
- the base perimeter is greater than the intermediate perimeter.
- the shell 20 preferably comprises a plurality of spaced apart reamer teeth 46.
- Each tooth 46 is formed from the reamer sidewall 34 that outwardly extends from the reamer shell exterior surface.
- each of the plurality of reamer shell teeth 46 comprises a tooth opening 48 that extends through the thickness of the shell sidewall 34.
- the tooth opening 48 allows for the removal of tissue debris during a reaming surgical procedure.
- a tissue cutting surface 50 is formed at a distal end 52 of each of the plurality of teeth 46 extending outwardly from the reamer shell exterior surface and positioned over the respective tooth opening 48.
- the plurality of reamer shell tissue cutting surfaces 50 is arranged in either a clockwise or counter-clockwise orientation about the rotational axis A-A.
- the reamer shell 20 comprises a flange 54 having a flange distal end 56 that extends from the intermediate perimeter to a flange proximal end 58 positioned within the shell interior.
- the flange 54 comprises a flange sidewall 60 constructed in an annular shape that extends circumferentially about the rotational axis A-A.
- the flange sidewall 60 comprises a flange thickness that extends between opposed interior, and exterior flange sidewall surfaces 62, 64.
- the flange sidewall 60 defines the intermediate perimeter of the shell opening 24 having an interior diameter 66 that extends between diametrically opposed flange sidewall interior surfaces 62, perpendicular to the rotational axis A-A.
- the flange interior diameter 66 is preferably dimensioned to receive the reamer insert 22.
- the interior flange diameter 66 may range from about 1 cm to about 10 cm.
- the flange sidewall 60 has a length 68 that extends in a proximal direction from the flange distal end 56 at the shell opening 24 to the flange proximal end 58.
- the length 68 of the flange sidewall 60 may range from about 1 cm to about 5 cm.
- the reamer shell 20 comprises at least one anchor 70 that is positioned at the reamer shell base 36.
- the anchor 70 extends outwardly from an anchor proximal end 72 at the reamer shell exterior surface to an anchor distal end 74 having an anchor tissue cutting surface 76.
- the anchor distal end 74 is positioned over an anchor opening 78 that extends through the thickness at the reamer shell base 36.
- the anchor opening 78 provides space for the flexure of the anchor distal end 74.
- the anchor opening 78 allows for the entry of bone or tissue to thereby help secure the shell 20 thereto.
- the at least one anchor 70 is configured to embed within surrounding tissue or bone thereby, temporarily immobilizing the reamer shell 20, and thus, allowing for independent rotation of the reamer insert 22 with respect to the reamer shell 20.
- the anchor tissue cutting surface 76 is oriented in an opposite direction as the tissue cutting surface 50 of the reamer shell cutting teeth 46, about the rotational axis A-A.
- This preferred anchor orientation allows for the shell 20 to ream bone and tissue without causing the anchor 70 to become embedded within tissue or bone.
- an exemplary bone cutter is configured with the reamer shell teeth 46 oriented in a clockwise direction and the anchor tissue cutting surface 76 oriented in the opposite, counterclockwise direction about the rotational axis A-A.
- rotation of the shell 20 in the clockwise direction enables the shell 20 to ream bone and tissue without causing the anchor 70 to become embedded within surrounding bone or tissue.
- Rotation in the opposite, counter-clockwise direction about the rotational axis A-A causes the anchor 70 to become embedded within surrounding tissue or bone, thereby immobilizing the reamer shell.
- Subsequent rotation of the shell 20 in an opposite direction, i.e., clockwise direction about rotational axis A-A causes the anchor 70 to become dislodged from the surrounding tissue and bone.
- immobilizing the reamer shell 20 allows for independent reaming of tissue and bone by rotation of the insert 22.
- FIGS. 4A and 4B illustrate an embodiment of the reamer insert 22 that is positioned within the reamer shell opening 24.
- the reamer insert 22 extends from an insert proximal end 80 to an insert distal end 82.
- the reamer insert 22 comprises an insert sidewall 84 ( FIG. 7 ) having an annular shape that meets a partial hemispherically shaped insert end wall 86 having opposed distal and proximal end wall surfaces 88, 90.
- the insert 22 is positioned within the reamer shell opening 24 with the insert distal end 82 oriented towards the apex 16 along the rotational axis A-A. As illustrated in FIGS.
- pins 92 outwardly extend in an opposing orientation from the exterior surface of the insert sidewall 84. As shown, four pins 92 outwardly extend from the insert sidewall exterior surface. In a preferred embodiment, the four pins 92 are positioned a distance spaced equally apart at the proximal end 80 of the insert 22.
- the insert end wall 86 comprises a plurality of spaced apart insert teeth 94, each tooth having a tissue cutting surface 96.
- each of the plurality of reamer insert teeth 94 is formed from the insert end wall 86 that outwardly extends from the insert end wall distal surface and provides for cutting a hemispherically shaped cavity within the acetabulum.
- each of the plurality of insert teeth 94 comprises a tooth opening 98 that extends through the thickness of the insert end wall 86. The opening 98 allows for the removal of tissue debris during a reaming surgical procedure.
- the tissue cutting surface 96 is formed at the distal end of each of the teeth 94 extending outwardly from the insert end wall distal surface 88 and is positioned over a respective tooth opening 98.
- the plurality of tissue cutting surfaces 96 of the reamer insert teeth 94 are oriented about the rotational axis A-A in an opposite direction to that of the tissue cutting surfaces 50 of the reamer shell teeth 46.
- the tissue cutting surfaces 96 of the insert teeth 94 are preferably oriented in the opposite, counter-clockwise direction about the rotational axis A-A.
- the tissue cutting surface 76 of the at least one anchor 70 is oriented in the same direction as the tissue cutting surfaces 96 of the insert teeth 94.
- the insert end wall 86 may have a curved construction. As illustrated in FIGS. 1 , 2 , 4A , 4B , and 7 , the insert end wall 86 preferably comprises a convex structure that outwardly extends in a distal direction. The curvature of the insert end wall 86 allows for the insert 22 to ream a cavity having a curved surface.
- the distal surface 88 of the insert end wall 86 may comprise a convex structure having a radius of curvature R 1 ( FIGS. 4A and 4B ) that ranges from about 1 cm to about 5 cm.
- R 1 radius of curvature
- the bone cutter 10 comprises a collar 100 that connects the reamer insert 22 to the reamer shell 20.
- the collar 100 has a collar proximal end 102 spaced from a collar distal end 104.
- the collar 100 comprises a sidewall 106 having a collar sidewall thickness that extends between opposed exterior and interior sidewall surfaces 108, 110.
- the collar 100 is preferably configured in an annular shape that defines a collar opening with an interior diameter 112 that extends between opposed interior collar sidewall surfaces 110 perpendicular to the rotational axis A-A.
- the collar interior diameter 112 is less than an outer diameter 114 of the flange 54.
- the collar 100 is preferably secured to the reamer shell flange 54. As illustrated in FIGS. 4A and 4B the collar 100 is positioned at the flange proximal end 58 such that at least a portion of the collar sidewall interior surface is in physical contact with a portion of the flange sidewall exterior surface, thus forming an interference fit therebetween.
- the collar 100 comprises at least two slots 116 ( FIGS. 8 and 9 ), that at least partially extend part-way through the collar thickness from the interior surface 110.
- the at least two slots 116 are dimensioned to each receive a reamer insert pin 92.
- the at least two collar slots 116 extend from the collar proximal end 102 to a position spaced from the collar distal end 104.
- each of the slots 116 is preferably orientated at an angle with respect to the rotational axis A-A.
- the slots 116 are oriented in a spiral orientation about the collar sidewall interior surface 110 with respect to the rotational axis A-A.
- the slots 116 extend from the collar proximal end 102 to a groove 118 having a ledge surface 120 positioned at the collar distal end 104.
- the groove 118 is formed part-way through the collar thickness from the interior surface 110.
- the groove 118 extends circumferentially about the annular collar sidewall 106 and rotational axis A-A.
- the ledge surface 120 provides a track on which the at least two insert pins 92 rotate about the rotational axis A-A within the collar opening.
- the groove 118 is connected to the slots 116 such that the pins 92 are capable of riding in and out of a respective slot 116 and then along the ledge surface 120.
- the at least two pins 92 ride within a respective slot 116 that are positioned in opposition to each other.
- the pins 92 are capable of riding within the slot 116 in a back and forth manner from the collar proximal end 102 to the ledge surface 120 at the collar distal end 104.
- the insert 22 rotates within the reamer shell opening 24 and travels in either a distal or proximal direction along the direction of the rotational axis A-A.
- the insert 22 may travel in a distal direction until the pins 92 exit their respective slot 116 and ride along the track formed by the groove 118.
- the pins 92 can ride along the track formed by the groove 118 so that the insert 22 is capable of 360° rotation.
- the insert 22 may be retracted within the reamer shell 20 by rotating the insert in an opposite direction, i.e., counter-clockwise, such that the pins 92 leave the groove 118 to enter and ride within a respective slot 116 traveling in a proximal direction towards the bone cutter base 12, thus, retracting the insert 22 within the reamer shell 20.
- the collar distal end 104 is secured to the reamer shell flange 54 such that rotational movement of the insert 22 within the reamer shell opening 24 is not impeded.
- the collar 100 is secured to the flange 54 such that there is a gap 122 ( FIG. 4A ) between the flange proximal end 58 and the surface 120 of the groove 118.
- the gap 122 is dimensioned to allow for travel of the pins 92 therewithin.
- the collar 100 may be secured to the flange 54 with an adhesive or by welding the collar 100 to the flange 54.
- the collar 100 may also be secured to the reamer shell flange 54 by a fastener (not shown).
- the fastener may at least partially extend through the thickness of the sidewalls of the collar 100 and reamer shell flange 54 to thus secure the reamer insert 22 within the shell opening 24.
- FIGS. 11 to 13 , 14A , and 14B illustrate an alternative embodiment of a bone cutter 124 of the present invention.
- the bone cutter 124 comprises an alternate embodiment of an insert 126 and collar 128.
- the bone cutter 124 comprises the reamer shell 20 ( FIG. 6 ) which comprises the shell opening 24, flange 54, and a plurality of spaced apart reamer teeth 46, as previously discussed.
- the collar 128 has a collar proximal end 130 spaced from a collar distal end 132 that connects the reamer insert 126 to the reamer shell 20.
- the collar 128 comprises a sidewall 134 having a collar sidewall thickness that extends between diametrically opposed exterior and interior sidewall surfaces 136, 138.
- the collar 128 is configured in an annular shape that defines a collar interior diameter 140 that extends between opposed interior collar sidewall surfaces 138 perpendicular to the rotational axis A-A.
- the collar 128 comprises at least two pins 142 that extend inwardly from the collar sidewall interior surface 138.
- the collar 128 is preferably fixedly secured to the reamer shell flange 54. As illustrated in FIGS. 14A and 14B , the collar is positioned at the flange proximal end 58 such that at least a portion of the collar sidewall interior surface is in physical contact with a portion of the flange sidewall exterior surface.
- FIGS. 11 , 12 , 14A , and 14B illustrate an embodiment of the insert 126 of the bone cutter 124.
- the reamer insert 126 extends from an insert proximal end 144 to an insert distal end 146.
- the reamer insert 126 comprises an insert sidewall 148 having an annular shape that meets a partial hemispherically shaped insert end wall 150 at the insert distal end 146.
- the insert 126 is positioned within the reamer shell opening 24 with the insert distal end 146 oriented towards the apex 16.
- the insert end wall 150 comprises a plurality of spaced apart insert teeth 156, each tooth having a tissue cutting surface 158.
- each of the teeth 156 is formed from an outwardly extending portion of the insert end wall 150.
- each tooth 156 resides adjacent to an opening 160 that extends through the thickness of the insert end wall 150. The opening 160 allows for the removal of tissue debris during a reaming surgical procedure.
- the tissue cutting surface 158 formed at the distal end of each of the teeth 156 extends outwardly from the insert end wall 150 and is positioned over a respective tooth opening 160.
- the plurality of tissue cutting surfaces 158 of the reamer insert teeth 156 are oriented about the rotational axis A-A in an opposite direction as that of the tissue cutting surfaces 50 of the reamer shell teeth 46.
- the tissue cutting surfaces 158 of the insert teeth 156 are preferably oriented in the opposite, counter-clockwise direction about the rotational axis A-A.
- the insert end wall 150 preferably comprises a convex structure that outwardly extends in a distal direction. The curvature of the insert end wall 150 thus allows for the insert 126 to ream a cavity having a curved surface.
- the insert end wall 150 may comprise a convex structure having a radius of curvature R 2 that ranges from about 1 cm to about 5 cm.
- the insert annular sidewall 148 comprises at least two slots 162 that extend part-way through the sidewall 148 thickness from exterior surface 164 thereof.
- Each of the at least two slots 162 is preferably oriented at an angle with respect to the rotational axis A-A.
- each of the at least two slots 162 is positioned in a spiral orientation with respect to the longitudinal axis A-A extending from the insert proximal end 144 to the insert distal end 146.
- the at least two slots 162 are configured to each receive a collar pin 142 that extends inwardly from the collar interior sidewall surface 138.
- a groove 166 is formed part-wat through the sidewall 148 thickness from the exterior surface 164 thereof resides at the insert proximal end 144.
- the groove 166 forms a track on which the collar pins 142 ride.
- the groove 166 is oriented perpendicular to the rotational axis A-A.
- the insert 126 is positioned within the interior of the collar 128 with each of the at least two collar pins 142 received within an insert slot 162, respectively.
- the at least two pins 142 ride within a respective insert slot 162 that is positioned in opposition to each other.
- the pins 142 are capable of riding within the insert slot 162 in a back and forth manner from the distal insert end 146 to the groove 166 at the insert proximal end 144. As the collar pins 142 ride within the slot 162, the insert 126 rotates within the reamer shell opening 24 traveling in either a distal or proximal direction.
- the insert 126 may travel in a distal direction until the pins 142 exit their respective slot 162 and ride along the track formed by the groove 166 at the insert proximal end 144.
- the collar pins 142 ride along the track formed by the groove 166 so that the insert 126 is capable of 360° rotation.
- the insert 126 may be retracted within the reamer shell 20 by rotating the insert in an opposite direction, i.e., counter-clockwise, such that the pins 142 leave the groove 166 to enter and ride within a respective slot 162 in a proximal direction so that the insert 126 retracts within the reamer shell 20.
- the collar 128 is secured to the reamer shell flange 54 that extends within the reamer shell 20.
- the collar distal end 132 is secured to the reamer shell flange proximal end 58 such that rotational movement of the insert 126 within the reamer shell opening 24 is not impeded.
- the collar 128 may be secured to the reamer shell flange 54 with an adhesive or by welding the collar 100 to the flange 54.
- the collar 100 may be secured to the reamer shell flange 54 by a fastener (not shown).
- the fastener (not shown) may at least partially extend through the thickness of the sidewalls of the collar 100 and reamer shell flange 54.
- a band 170 ( FIGS. 11 , 14A , and 14B ) having an annular band sidewall 172 with opposed interior and exterior sidewall surfaces 174, 176, is positioned at the collar proximal end 130.
- the band 170 preferably helps hold the insert 126 within the collar 100.
- the band 170 comprises a band inner diameter 178 extending between diametrically opposed interior surfaces 174 perpendicular to the rotational axis A-A.
- the band inner diameter 178 is greater than the outer diameter of the insert sidewall 84 and the outer diameter of the collar sidewall 134.
- the insert 126 is positioned within a collar opening defined by the annular collar sidewall 134 such that the insert 126 is capable of rotating therewithin.
- the collar 100 is secured to the flange 54 of the reamer shell 20.
- the band 170 is positioned so that the proximal ends of the collar 100 and insert 126 fit within the interior diameter 178 of the band 170.
- the band 170 may comprise a lip 180 that is designed to support the proximal end 130 of the collar 100.
- the lip 180 extends circumferentially about the band sidewall interior surface 174 and serves as a stop to prevent the insert 126 from separating from the reamer shell 20.
- the lip 180 extends about perpendicular to the rotational axis A-A.
- FIGS. 10 and 12 illustrate two different embodiments of a driver interface that connects with the driver shaft of a rotary power tool to thereby impart rotational movement to the bone cutters 10, 124.
- a driver interface 182 is of a crossbar design. Specifically, the driver interface 182 comprises a first bar 184 and second bar 186 that are orientated perpendicularly to each other. In the embodiment shown, the bars 184, 186 are of a curved cross-section perpendicular to their length.
- the bars 184, 186 are positioned within the base portion of the insert 22, 126, the respective insert annular sidewalls 84, 148 extending circumferentially around the bars 184, 186.
- FIG. 12 illustrates an alternative embodiment of a driver interface 188.
- the driver interface 188 comprises a bar and boss interface.
- This driver interface 188 comprises a bar portion 190 extending to a boss 192.
- the boss 192 has opposed semi-circular sides meeting the bar portion 190. Similar to the previous crossed bar driver interface 182, the bar and boss interface 188 may extend across the diameter of the base portion of the insert 22, 126.
- FIGS. 16A and 16B illustrate embodiments of the operation of the bone cutters 10, 124, of the present invention.
- either embodiment of the bone cutter 10, 124 is preferably positioned within an opening of the body near the acetabulum with the insert 22, 126 in a retracted positioned within the interior of the shell 20.
- the retracted position is defined as when the insert tissue cutting surfaces 96, 158 are positioned within the shell interior below the shell opening perimeter.
- the shell 20 of the bone cutter 10, 124 is rotated in the direction of the reamer shell tissue cutting surfaces 96, 158, in either a clockwise or counterclockwise direction. This allows for the reamer shell to cut tissue and/or bone such as the acetabular roof 28 and acetabular labrum 30.
- the reamer shell 20 is rotated in the opposite direction to thereby anchor the reamer shell within surrounding tissue and/or bone.
- the insert 22, 126 is continued to be rotated in the same direction to extend the insert tissue cutting teeth 94, 156 from within the shell interior.
- the insert is rotated in the opposite direction of the orientation of the shell cutting teeth 46 to extend the insert cutting teeth 94, 156 past the reamer shell opening 24.
- the insert 22, 126 is continued to be rotated so that acetabular floor and fossa are adequately reamed to the appropriate diameter.
- the reamer insert is then rotated in the opposite direction to retract the insert cutting teeth 94, 156 into the reamer shell interior.
- the bone cutter anchors 70 are dislodged from the surrounding bone and tissue and the bone cutter 10, 124 is removed from the body.
- the reamer shell 20, inserts 22, 126, collars 100, 128 and band 170 are composed of a biocompatible material. More specifically, at least one of the reamer shell 20, inserts 22, 126, collars 100, 128 and band 170 may be composed of a biocompatible polymer, metal or ceramic material. Examples of such polymeric materials include, but are not limited to, acrylonitrile butadiene styrene (ABS), polyacrylamides (PARA), polyetherimide (PEI), and polyetheretherketone (PEEK). In addition, examples of metallic materials include, but are not limited to, stainless steel, titanium, MP35N, and a biocompatible metal.
- the invention includes the following numbered recitations 1 to 30:
Abstract
Description
- This application claims priority from
U.S. Provisional Patent Application Serial No. 62/266,342, filed December 11, 2015 - The present invention relates to the art of orthopedic cutting devices, more particularly, to an orthopedic cutting device designed to remove bone and tissue from the acetabulum.
- Reamers are devices intended to remove tissue and bone from the human body. Similarly to that of a traditional reamer device, the orthopedic cutting device of the present invention is designed to remove bone and tissue from the cotyloid cavity or acetabulum in preparation for the insertion of a prosthetic cup during hip arthroplasty.
- The cotyloid cavity is a cup shaped cavity at the base of the hipbone into which the ball-shaped head of the femur is received (
FIG. 15 ). The acetabulum comprises an acetabulum bone floor that extends to the acetabular roof, the bone structure that resides along the upper portion of the cotyloid cavity.
The acetabular fossa, a depressed area having a relatively thin bone structure, resides about the center of the acetabular floor. The acetabular labrum, a ring of fibrous cartilage, resides along the outer perimeter of the cotyloid cavity. - Traditional prior art acetabular reamers, such as the one disclosed in
U.S. Pat. No. 5,709,688 to Salyer, are generally constructed having a rigid hemispherical shell structure with a continuous hemispherical surface. A plurality of spaced apart teeth, arranged in the same direction, outwardly extend from the shell exterior. The hemispherical structure is suited to create a cavity within the acetabulum which receives a prosthetic cup. Prosthetic cups generally have a curved exterior surface that is inserted into the cotyloid cavity. - During a traditional total hip arthroplasty procedure, a series of prior art reamers are used to form a hemispherically shaped cavity within the acetabulum. The series of prior art reamers of increasing diameter are typically used to gradually form a hemispherical cavity, reaming from the acetabular floor and fossa outwards to the acetabular labrum until a desired diameter is reached. Prior art orthopedic reamers are typically fabricated as modular units that are sold in a set of an array of diameters. These reamer tool sets are generally manufactured with reamer cutting heads providing bore sizes ranging from about 36 mm to about 80 mm in 1 mm increments sometimes totaling over 45 sizes. Since it is desirable to achieve a close prosthetic fit, a wide array of reaming tools of varying sizes are required to be on hand to provide the most precise cut and optimum bore diameter.
- The rigid hemispherical shape of prior art reamers causes the hemispherical cavity to gradually be formed of increasing diameter from the acetabular fossa at the center of the acetabular floor outwards to the acetabular roof. Each time a different reamer is inserted, the reamer apex contacts and abrades the acetabular floor and fossa. Such a procedure is believed to remove excessive bone from the acetabular fossa, thus resulting in a reamed acetabulum having reduced strength and rigidity. In addition, the insertion and removal of multiple prior art reamers may potentially lead to infection. Furthermore, the procedure of inserting and removing multiple prior art reamers is potentially traumatic to the body.
- The present invention addresses these potential problems by providing a bone cutter that is configured to ream the cotyloid cavity with one device. In contrast to prior art reamers, the bone cutter of the present invention is designed to ream the acetabular roof and acetabular labrum prior to significantly reaming the acetabular floor and acetabular fossa. Therefore, abrasion to the acetabular floor and fossa is reduced, thus resulting in the preservation of more of the acetabular floor and fossa bone structure. As a result, the bone structure of the reamed acetabulum has greater strength and rigidity in comparison to an acetabulum that is reamed by the prior art procedure with the prior art reamers. Furthermore, since the bone cutter of the present invention eliminates the need to introduce and remove multiple prior art reamers, the risk of infection and trauma is minimized.
- Many minimally invasive prior art reamers have been designed in an attempt to minimize surgical trauma to the patient. Among these prior art reamer designs is the device disclosed in
U.S. Pat. No. 7,850,692 to White et al. , which is assigned to the assignee of the present invention and incorporated herein by reference. White discloses an acetabular reamer having a reduced "lemon wedge shaped" profile so that it can pass through an incision of a reduced opening size. - However, in contrast to the bone cutter of the present invention, the acetabular reamer of White comprises a fixed rigid reamer shell that necessitates the use of multiple reamer devices to create a hemispherical cavity of a desired diameter. Furthermore, the rigid partial hemispherical design may cause additional abrasion of the acetabular fossa and floor as the apex of the multitude of increasingly large reamers come into contact with the acetabular floor surface.
- Another prior art acetabular reamer is disclosed in
U.S. Pat. No. 7,608,076 to Ezzedine , which is assigned to the assignee of the present invention and incorporated herein by reference. Ezzedine discloses a collapsible surgical reamer having a hinge along its rotating axis. While the collapsed configuration allows for the device to pass through a minimally invasive incision, the Ezzedine device must be in an unfolded configuration to ream bone and tissue. Thus, the Ezzedine reamer comprises a rigid hemispherical shape having teeth that extend from the hemispherical structure when used within the body. In addition, similar to the other prior art reamer devices, multiple reamers of increasing diameters are required to be inserted and removed from the body to create a cavity of a desired diameter. Thus, the rigid hemispherical structure of the Ezzedine reamer may cause additional abrasion to the acetabular floor and fossa during a procedure which may potentially cause the acetabulum to become less rigid. - Yet another embodiment of an acetabular reamer is disclosed by
Sherry et al. in U.S. Pat. No. 8,052,689 , which is assigned to the assignee of the present invention and incorporated herein by reference. Sherry discloses an acetabular reamer having a truncated cutting shell that is constructed without an apex.
The omission of the apex from the reamer shell allows for the reaming of the acetabular roof and acetabular labrum without contacting the acetabular fossa. However, in order to form a full hemispherical cavity within the acetabulum, the Sherry device must be rocked in a back and forth manner for the cutting teeth to contact the acetabular floor region. Such a rocking motion is not preferred as this may not produce a true hemispherical cavity. Furthermore, the rocking motion of the reamer within the body may aggravate and traumatize surrounding tissue. - The '689 to Sherry et al. patent discloses an alternate embodiment comprising a cap or plate that is positioned over the apex opening. As disclosed by Sherry, the cap or plate is stationary, but separately attached to the shell. Thus, in order to attach the cap or plate, the shell must either be removed from the body or manipulated by the surgeon within the body. In either case, the removal and insertion or the manipulation of the shell within the body to attach the apex cap may cause additional trauma or result in infection to the patient.
- In contrast to the prior art reamer device, the bone cutter of the present invention comprises a bone cutting insert that extends and retracts from within an opening that extends through the reamer shell. In addition, the bone cutter of the present invention is configured such that the insert is capable of rotational and axial movement independent of the reamer shell. Thus, when the insert is retracted within the reamer shell, the bone cutter is configured to ream the acetabular labrum and roof. The acetabular fossa or floor may then be reamed by outwardly extending the insert from within the reamer shell without removing the bone cutter from the body. Furthermore, the retracted configuration of the bone cutter of the present invention provides for insertion within a minimally invasive incision.
- Thus, the present invention provides a reamer that incorporates design features which address various limitations of the prior art. The features of the bone cutter of the present invention enable the reaming of the acetabular roof and the acetabular floor in separate steps without removal of the device from the body, thus more of the bone structure of the acetabulum preserved while minimizing patient trauma and infection.
- The present invention is an orthopedic cutting device designed to cut and remove tissue and bone material. The device is designed to efficiently remove tissue and bone from the cotyloid cavity for the insertion of an orthopedic implant.
- In an embodiment, the bone cutter comprises a reamer shell and a reamer insert that resides within an opening that extends through the apex of the reamer shell. The insert is capable of independent axial and rotational movement within the shell opening. The reamer shell is preferably of a partially hemispherical structure comprising a plurality of spaced apart shell teeth, each having a tissue cutting surface that extends outwardly from the reamer shell exterior surface. The insert preferably comprises an annular sidewall that meets an insert end wall that comprises a plurality of spaced apart insert cutting teeth having a tissue cutting surface.
- In an embodiment, the insert rides within a pin and slot mechanism that is positioned within the shell interior. This pin and slot mechanism provides axial and rotational movement of the insert with respect to the shell. In an embodiment, the insert is positioned within a collar that is secured within the reamer interior. The collar comprises an annular sidewall having a slot extending to a groove formed at least partially within the collar sidewall interior surface. A pin extending from the insert sidewall is received within the collar slot and rides therewithin. In an alternate embodiment, the insert is positioned within a collar that is secured within the reamer interior. The collar comprising an annular sidewall having at least one pin that extends outwardly from the collar sidewall interior surface. The insert comprising an insert sidewall having a slot extending to a groove is formed at least partially within the insert sidewall exterior surface. The pin extending from the collar sidewall interior surface is received within the insert slot and rides therewithin.
- When the insert is in a retracted position the bone cutter is configured to ream the acetabular roof. In addition, the retracted configuration provides a low profile orientation that helps allow for the insertion of the reamer through a minimally invasive incision. When the insert is in an extended position, the bone cutter is configured to ream the acetabular floor. Thus, the bone cutter of the present invention provides for the separate reaming of the acetabular roof and floor without the need to remove the device from the body.
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FIG. 1 illustrates a perspective view of an embodiment of the bone cutter of the present invention in an extended position. -
FIG. 1B is an enlarged view of an embodiment of a reamer shell anchor. -
FIG. 2 shows an embodiment of the bone cutter of the present invention in a retracted position. -
FIG. 3 illustrates an embodiment of the proximal end of the bone cutter of the present invention. -
FIG. 4A is a cross-sectional view of the embodiment of the bone cutter of the present invention illustrated inFIG. 1 with the insert in a retracted position. -
FIG. 4B is a cross-sectional view of the embodiment of the bone cutter of the present invention illustrated inFIG. 1 with the insert in an extended position. -
FIG. 5 is an exploded view of the embodiment of the bone cutter of the present invention shown inFIG. 1 . -
FIG. 6 illustrates a perspective view of an embodiment of the reamer shell component of the bone cutter of the present invention. -
FIG. 7 illustrates a perspective view of an embodiment of an insert component of the bone cutter of the present invention. -
FIG. 8 shows an embodiment of a collar component of the bone cutter of the present invention. -
FIG. 9 is a cross-sectional view of the collar component shown inFIG. 8 . -
FIG. 10 illustrates an embodiment of an insert component shown from the proximal end. -
FIG. 11 shows an exploded view of an embodiment of a bone cutter of the present invention. -
FIG. 12 illustrates an embodiment of an insert component of a bone cutter of the present invention. -
FIG. 13 illustrates an embodiment of a collar component of a bone cutter of the present invention. -
FIG. 14A is a cross-sectional view of an embodiment of a bone cutter of the present invention with the insert in a retracted position. -
FIG. 14B is a cross-sectional view of an embodiment of a bone cutter of the present invention with the insert in an extended position. -
FIG. 15 illustrates an embodiment of the acetabulum. -
FIG. 16A is a cross-sectional view of an embodiment of the bone cutter of the present invention positioned within the acetabulum with the insert in a retracted position. -
FIG. 16B is a cross-sectional view of an embodiment of the bone cutter of the present invention positioned within the acetabulum with the insert in an extended position. - Now turning to the figures,
FIGS. 1 to 3 ,4A ,4B , and5 illustrate an embodiment of abone cutter 10 of the present invention. Thebone cutter 10 extends from abone cutter base 12 at aproximal end 14 to an apex 16 at adistal end 18. An imaginary rotational axis A-A extends through the apex 16. In an embodiment, thebone cutter 10 comprises areamer shell 20, and areamer insert 22. Both thereamer shell 20 and insert 22 are configured to cut bone and tissue. In an embodiment, thereamer insert 22 is positioned within an opening 24 (FIG. 6 ) that extends through a thickness of theshell 20 adjacent to the apex 16. - The
insert 22 is designed to rotate either in a clockwise or counter-clockwise direction independent of thereamer shell 20 within theopening 24. In addition, theinsert 22 is configured to move in an axial direction along the rotational axis A-A within theshell opening 24. Theshell 20 is configured to ream the acetabular roof and labrum while the movablebone cutting insert 22 enables independent reaming of the acetabular floor and fossa. Thebone cutter 10 of the present invention thus eliminates the need to remove and insert multiple reamers of increasing diameter during a procedure. Therefore, the possibility that surgical trauma or infection may result is minimized. Furthermore, theinsert 22 may be positioned below theshell opening 24 within the shell interior thus providing thebone cutter 10 of the present invention with a low profile that is minimally invasive to insert and remove from the body. - In the case of reaming the acetabulum 26 during a hip replacement procedure as shown in
FIGS. 15 ,16A , and16B , theretractable reamer insert 22 allows for the reaming of theacetabular roof 28 andacetabular labrum 30 prior to the reaming of theacetabular fossa 32 which resides within the acetabular floor. As discussed by K De Smet et al. on page 326 of, The hip resurfacing handbook: A practical guide to the use and management of modern hip resurfacings, 2013, reaming theacetabular labrum 28 prior to theacetabular fossa 30 during a hip replacement surgical procedure is beneficial as it preserves more of the acetabulum bone structure. -
FIG. 6 illustrates an embodiment of thereamer shell 20. As shown, thereamer shell 20 comprises asidewall 34 having a curvature comprising a partial hemispherical shape that extends from ashell base 36 having abase edge 38, that defines a shell base perimeter at a shellproximal end 40. Thesidewall 34 extends from the base 36 towards an intermediate edge that defines an intermediate perimeter at a shelldistal end 42. The intermediate perimeter is located on an imaginary intermediate plane that is spaced from and positioned between theimaginary apex 16 and thebase edge 38. The intermediate perimeter defines theopening 24 having aregion 44 that radially extends from the imaginary rotational axis A-A at thebone cutter apex 16. In an embodiment, the base perimeter is greater than the intermediate perimeter. - The
shell 20 preferably comprises a plurality of spaced apartreamer teeth 46. Eachtooth 46 is formed from thereamer sidewall 34 that outwardly extends from the reamer shell exterior surface. In addition, each of the plurality ofreamer shell teeth 46 comprises atooth opening 48 that extends through the thickness of theshell sidewall 34. Thetooth opening 48 allows for the removal of tissue debris during a reaming surgical procedure. Atissue cutting surface 50 is formed at adistal end 52 of each of the plurality ofteeth 46 extending outwardly from the reamer shell exterior surface and positioned over therespective tooth opening 48. In an embodiment, the plurality of reamer shell tissue cutting surfaces 50 is arranged in either a clockwise or counter-clockwise orientation about the rotational axis A-A. - As illustrated in
FIGS. 4A ,4B ,5 , and6 , thereamer shell 20 comprises aflange 54 having a flangedistal end 56 that extends from the intermediate perimeter to a flangeproximal end 58 positioned within the shell interior. In an embodiment, theflange 54 comprises aflange sidewall 60 constructed in an annular shape that extends circumferentially about the rotational axis A-A. In an embodiment, theflange sidewall 60 comprises a flange thickness that extends between opposed interior, and exterior flange sidewall surfaces 62, 64. In a preferred embodiment, theflange sidewall 60 defines the intermediate perimeter of theshell opening 24 having aninterior diameter 66 that extends between diametrically opposed flange sidewall interior surfaces 62, perpendicular to the rotational axis A-A. The flangeinterior diameter 66 is preferably dimensioned to receive thereamer insert 22. In a preferred embodiment, theinterior flange diameter 66 may range from about 1 cm to about 10 cm. In addition, theflange sidewall 60 has alength 68 that extends in a proximal direction from the flangedistal end 56 at theshell opening 24 to the flangeproximal end 58. In a preferred embodiment, thelength 68 of theflange sidewall 60 may range from about 1 cm to about 5 cm. - In an embodiment, illustrated in
FIG. 1B , thereamer shell 20 comprises at least oneanchor 70 that is positioned at thereamer shell base 36. As shown, theanchor 70 extends outwardly from an anchorproximal end 72 at the reamer shell exterior surface to an anchordistal end 74 having an anchortissue cutting surface 76. As shown inFIG. 1B , the anchordistal end 74 is positioned over ananchor opening 78 that extends through the thickness at thereamer shell base 36. Theanchor opening 78 provides space for the flexure of the anchordistal end 74. In addition, the anchor opening 78 allows for the entry of bone or tissue to thereby help secure theshell 20 thereto. In a preferred embodiment, the at least oneanchor 70 is configured to embed within surrounding tissue or bone thereby, temporarily immobilizing thereamer shell 20, and thus, allowing for independent rotation of thereamer insert 22 with respect to thereamer shell 20. - In a preferred embodiment, the anchor
tissue cutting surface 76 is oriented in an opposite direction as thetissue cutting surface 50 of the reamershell cutting teeth 46, about the rotational axis A-A. This preferred anchor orientation allows for theshell 20 to ream bone and tissue without causing theanchor 70 to become embedded within tissue or bone. For example, an exemplary bone cutter is configured with thereamer shell teeth 46 oriented in a clockwise direction and the anchortissue cutting surface 76 oriented in the opposite, counterclockwise direction about the rotational axis A-A. Thus, rotation of theshell 20 in the clockwise direction enables theshell 20 to ream bone and tissue without causing theanchor 70 to become embedded within surrounding bone or tissue. Rotation in the opposite, counter-clockwise direction about the rotational axis A-A, however, causes theanchor 70 to become embedded within surrounding tissue or bone, thereby immobilizing the reamer shell. Subsequent rotation of theshell 20 in an opposite direction, i.e., clockwise direction about rotational axis A-A, causes theanchor 70 to become dislodged from the surrounding tissue and bone. In an embodiment, immobilizing thereamer shell 20 allows for independent reaming of tissue and bone by rotation of theinsert 22. -
FIGS. 4A and4B illustrate an embodiment of thereamer insert 22 that is positioned within thereamer shell opening 24. As shown, thereamer insert 22 extends from an insertproximal end 80 to an insertdistal end 82. Thereamer insert 22 comprises an insert sidewall 84 (FIG. 7 ) having an annular shape that meets a partial hemispherically shapedinsert end wall 86 having opposed distal and proximal end wall surfaces 88, 90. In a preferred embodiment, theinsert 22 is positioned within the reamer shell opening 24 with the insertdistal end 82 oriented towards the apex 16 along the rotational axis A-A. As illustrated inFIGS. 4A ,4B ,5 , and7 , at least twopins 92, outwardly extend in an opposing orientation from the exterior surface of theinsert sidewall 84. As shown, fourpins 92 outwardly extend from the insert sidewall exterior surface. In a preferred embodiment, the fourpins 92 are positioned a distance spaced equally apart at theproximal end 80 of theinsert 22. - In an embodiment, the
insert end wall 86 comprises a plurality of spaced apart insertteeth 94, each tooth having atissue cutting surface 96. In an embodiment, each of the plurality ofreamer insert teeth 94 is formed from theinsert end wall 86 that outwardly extends from the insert end wall distal surface and provides for cutting a hemispherically shaped cavity within the acetabulum. In addition, each of the plurality ofinsert teeth 94 comprises atooth opening 98 that extends through the thickness of theinsert end wall 86. Theopening 98 allows for the removal of tissue debris during a reaming surgical procedure. In an embodiment, thetissue cutting surface 96 is formed at the distal end of each of theteeth 94 extending outwardly from the insert end walldistal surface 88 and is positioned over arespective tooth opening 98. In an embodiment, the plurality of tissue cutting surfaces 96 of thereamer insert teeth 94 are oriented about the rotational axis A-A in an opposite direction to that of the tissue cutting surfaces 50 of thereamer shell teeth 46. For example, if the tissue cutting surfaces 50 of thereamer shell teeth 46 are oriented in a clockwise direction about the rotational axis A-A, the tissue cutting surfaces 96 of theinsert teeth 94 are preferably oriented in the opposite, counter-clockwise direction about the rotational axis A-A. Furthermore, thetissue cutting surface 76 of the at least oneanchor 70 is oriented in the same direction as the tissue cutting surfaces 96 of theinsert teeth 94. - In an embodiment, the
insert end wall 86 may have a curved construction. As illustrated inFIGS. 1 ,2 ,4A ,4B , and7 , theinsert end wall 86 preferably comprises a convex structure that outwardly extends in a distal direction. The curvature of theinsert end wall 86 allows for theinsert 22 to ream a cavity having a curved surface. In an embodiment, thedistal surface 88 of theinsert end wall 86 may comprise a convex structure having a radius of curvature R1 (FIGS. 4A and4B ) that ranges from about 1 cm to about 5 cm. In a preferred embodiment, when theinsert 22 is in an extended position, such that theinsert cutting teeth 94 are positioned above theshell opening 24, the curvature of the insertdistal end 82 forms thebone cutter apex 16. - In an embodiment, as shown in
FIGS. 4A ,4B ,5 ,8, and 9 , thebone cutter 10 comprises acollar 100 that connects thereamer insert 22 to thereamer shell 20. As illustrated, thecollar 100 has a collarproximal end 102 spaced from a collardistal end 104. In an embodiment, thecollar 100 comprises asidewall 106 having a collar sidewall thickness that extends between opposed exterior and interior sidewall surfaces 108, 110. Thecollar 100 is preferably configured in an annular shape that defines a collar opening with aninterior diameter 112 that extends between opposed interior collar sidewall surfaces 110 perpendicular to the rotational axis A-A. In an embodiment, the collarinterior diameter 112 is less than anouter diameter 114 of theflange 54. In an embodiment, thecollar 100 is preferably secured to thereamer shell flange 54. As illustrated inFIGS. 4A and4B thecollar 100 is positioned at the flangeproximal end 58 such that at least a portion of the collar sidewall interior surface is in physical contact with a portion of the flange sidewall exterior surface, thus forming an interference fit therebetween. - In an embodiment, the
collar 100 comprises at least two slots 116 (FIGS. 8 and 9 ), that at least partially extend part-way through the collar thickness from theinterior surface 110. The at least twoslots 116 are dimensioned to each receive areamer insert pin 92. As illustrated inFIGS. 8 and 9 , the at least twocollar slots 116 extend from the collarproximal end 102 to a position spaced from the collardistal end 104. In an embodiment, each of theslots 116 is preferably orientated at an angle with respect to the rotational axis A-A. In a preferred embodiment, theslots 116 are oriented in a spiral orientation about the collar sidewallinterior surface 110 with respect to the rotational axis A-A. - In an embodiment, as illustrated in
FIGS. 8 and 9 , theslots 116 extend from the collarproximal end 102 to agroove 118 having aledge surface 120 positioned at the collardistal end 104. In a preferred embodiment, thegroove 118 is formed part-way through the collar thickness from theinterior surface 110. Thegroove 118 extends circumferentially about theannular collar sidewall 106 and rotational axis A-A. Theledge surface 120, provides a track on which the at least two insert pins 92 rotate about the rotational axis A-A within the collar opening. In an embodiment, thegroove 118 is connected to theslots 116 such that thepins 92 are capable of riding in and out of arespective slot 116 and then along theledge surface 120. In an embodiment, the at least twopins 92 ride within arespective slot 116 that are positioned in opposition to each other. In a preferred embodiment, thepins 92 are capable of riding within theslot 116 in a back and forth manner from the collarproximal end 102 to theledge surface 120 at the collardistal end 104. As thepins 92 ride within arespective slot 116, theinsert 22 rotates within thereamer shell opening 24 and travels in either a distal or proximal direction along the direction of the rotational axis A-A. For example, as theinsert 22 is rotated in a clockwise direction, the insert may travel in a distal direction until thepins 92 exit theirrespective slot 116 and ride along the track formed by thegroove 118. In a preferred embodiment, thepins 92 can ride along the track formed by thegroove 118 so that theinsert 22 is capable of 360° rotation.
In an embodiment, theinsert 22 may be retracted within thereamer shell 20 by rotating the insert in an opposite direction, i.e., counter-clockwise, such that thepins 92 leave thegroove 118 to enter and ride within arespective slot 116 traveling in a proximal direction towards thebone cutter base 12, thus, retracting theinsert 22 within thereamer shell 20. - In an embodiment, the collar
distal end 104 is secured to thereamer shell flange 54 such that rotational movement of theinsert 22 within thereamer shell opening 24 is not impeded. In a preferred embodiment, thecollar 100 is secured to theflange 54 such that there is a gap 122 (FIG. 4A ) between the flangeproximal end 58 and thesurface 120 of thegroove 118. Thegap 122 is dimensioned to allow for travel of thepins 92 therewithin. In an embodiment, thecollar 100 may be secured to theflange 54 with an adhesive or by welding thecollar 100 to theflange 54. Thecollar 100 may also be secured to thereamer shell flange 54 by a fastener (not shown). In an embodiment, the fastener (not shown) may at least partially extend through the thickness of the sidewalls of thecollar 100 andreamer shell flange 54 to thus secure thereamer insert 22 within theshell opening 24. -
FIGS. 11 to 13 ,14A , and14B , illustrate an alternative embodiment of abone cutter 124 of the present invention. As shown, thebone cutter 124 comprises an alternate embodiment of aninsert 126 andcollar 128. In addition, thebone cutter 124 comprises the reamer shell 20 (FIG. 6 ) which comprises theshell opening 24,flange 54, and a plurality of spaced apartreamer teeth 46, as previously discussed. In an embodiment, thecollar 128 has a collarproximal end 130 spaced from a collardistal end 132 that connects thereamer insert 126 to thereamer shell 20. As illustrated, thecollar 128 comprises asidewall 134 having a collar sidewall thickness that extends between diametrically opposed exterior and interior sidewall surfaces 136, 138. Thecollar 128 is configured in an annular shape that defines a collarinterior diameter 140 that extends between opposed interior collar sidewall surfaces 138 perpendicular to the rotational axis A-A. In an embodiment, thecollar 128 comprises at least twopins 142 that extend inwardly from the collar sidewallinterior surface 138. In an embodiment, thecollar 128 is preferably fixedly secured to thereamer shell flange 54. As illustrated inFIGS. 14A and14B , the collar is positioned at the flangeproximal end 58 such that at least a portion of the collar sidewall interior surface is in physical contact with a portion of the flange sidewall exterior surface. -
FIGS. 11 ,12 ,14A , and14B , illustrate an embodiment of theinsert 126 of thebone cutter 124. As shown, thereamer insert 126 extends from an insertproximal end 144 to an insertdistal end 146. Thereamer insert 126 comprises aninsert sidewall 148 having an annular shape that meets a partial hemispherically shapedinsert end wall 150 at the insertdistal end 146. In a preferred embodiment, theinsert 126 is positioned within the reamer shell opening 24 with the insertdistal end 146 oriented towards the apex 16. - Similar to the embodiment of the
insert 22 of thebone cutter 10, theinsert end wall 150 comprises a plurality of spaced apart insertteeth 156, each tooth having atissue cutting surface 158. In an embodiment, each of theteeth 156 is formed from an outwardly extending portion of theinsert end wall 150. In addition, eachtooth 156 resides adjacent to anopening 160 that extends through the thickness of theinsert end wall 150. Theopening 160 allows for the removal of tissue debris during a reaming surgical procedure. Thetissue cutting surface 158 formed at the distal end of each of theteeth 156 extends outwardly from theinsert end wall 150 and is positioned over arespective tooth opening 160. In an embodiment, the plurality of tissue cutting surfaces 158 of thereamer insert teeth 156 are oriented about the rotational axis A-A in an opposite direction as that of the tissue cutting surfaces 50 of thereamer shell teeth 46. For example, if the tissue cutting surfaces 50 of thereamer shell teeth 46 are oriented in a clockwise direction about the rotational axis A-A, the tissue cutting surfaces 158 of theinsert teeth 156 are preferably oriented in the opposite, counter-clockwise direction about the rotational axis A-A. Theinsert end wall 150 preferably comprises a convex structure that outwardly extends in a distal direction. The curvature of theinsert end wall 150 thus allows for theinsert 126 to ream a cavity having a curved surface. In an embodiment, theinsert end wall 150 may comprise a convex structure having a radius of curvature R2 that ranges from about 1 cm to about 5 cm. - In an embodiment, the insert
annular sidewall 148 comprises at least twoslots 162 that extend part-way through thesidewall 148 thickness fromexterior surface 164 thereof. Each of the at least twoslots 162 is preferably oriented at an angle with respect to the rotational axis A-A. In a preferred embodiment, each of the at least twoslots 162 is positioned in a spiral orientation with respect to the longitudinal axis A-A extending from the insertproximal end 144 to the insertdistal end 146. In an embodiment, the at least twoslots 162 are configured to each receive acollar pin 142 that extends inwardly from the collarinterior sidewall surface 138. Agroove 166 is formed part-wat through thesidewall 148 thickness from theexterior surface 164 thereof resides at the insertproximal end 144. Thegroove 166 forms a track on which the collar pins 142 ride. In an embodiment, thegroove 166 is oriented perpendicular to the rotational axis A-A. - In an embodiment, the
insert 126 is positioned within the interior of thecollar 128 with each of the at least twocollar pins 142 received within aninsert slot 162, respectively. In an embodiment, the at least twopins 142 ride within arespective insert slot 162 that is positioned in opposition to each other. In a preferred embodiment, thepins 142 are capable of riding within theinsert slot 162 in a back and forth manner from thedistal insert end 146 to thegroove 166 at the insertproximal end 144. As the collar pins 142 ride within theslot 162, theinsert 126 rotates within thereamer shell opening 24 traveling in either a distal or proximal direction. For example, as theinsert 126 is rotated in a clockwise direction, the insert may travel in a distal direction until thepins 142 exit theirrespective slot 162 and ride along the track formed by thegroove 166 at the insertproximal end 144. In a preferred embodiment, the collar pins 142 ride along the track formed by thegroove 166 so that theinsert 126 is capable of 360° rotation. In an embodiment, theinsert 126 may be retracted within thereamer shell 20 by rotating the insert in an opposite direction, i.e., counter-clockwise, such that thepins 142 leave thegroove 166 to enter and ride within arespective slot 162 in a proximal direction so that theinsert 126 retracts within thereamer shell 20. - In an embodiment, the
collar 128 is secured to thereamer shell flange 54 that extends within thereamer shell 20. In an embodiment, the collardistal end 132 is secured to the reamer shell flangeproximal end 58 such that rotational movement of theinsert 126 within thereamer shell opening 24 is not impeded. In a preferred embodiment, thecollar 128 may be secured to thereamer shell flange 54 with an adhesive or by welding thecollar 100 to theflange 54. Thecollar 100 may be secured to thereamer shell flange 54 by a fastener (not shown). In an embodiment, the fastener (not shown) may at least partially extend through the thickness of the sidewalls of thecollar 100 andreamer shell flange 54. - A band 170 (
FIGS. 11 ,14A , and14B ) having anannular band sidewall 172 with opposed interior and exterior sidewall surfaces 174, 176, is positioned at the collarproximal end 130. Theband 170 preferably helps hold theinsert 126 within thecollar 100. In an embodiment, theband 170 comprises a bandinner diameter 178 extending between diametrically opposedinterior surfaces 174 perpendicular to the rotational axis A-A. In an embodiment, the bandinner diameter 178 is greater than the outer diameter of theinsert sidewall 84 and the outer diameter of thecollar sidewall 134. In an embodiment illustrated inFIGS. 14A and14B , theinsert 126 is positioned within a collar opening defined by theannular collar sidewall 134 such that theinsert 126 is capable of rotating therewithin. Thecollar 100 is secured to theflange 54 of thereamer shell 20. In an embodiment, theband 170 is positioned so that the proximal ends of thecollar 100 and insert 126 fit within theinterior diameter 178 of theband 170. In a preferred embodiment, theband 170 may comprise alip 180 that is designed to support theproximal end 130 of thecollar 100. In an embodiment, thelip 180 extends circumferentially about the band sidewallinterior surface 174 and serves as a stop to prevent theinsert 126 from separating from thereamer shell 20. In a preferred embodiment, thelip 180 extends about perpendicular to the rotational axis A-A. - The
bone cutters FIGS. 10 and12 illustrate two different embodiments of a driver interface that connects with the driver shaft of a rotary power tool to thereby impart rotational movement to thebone cutters FIG. 10 , adriver interface 182 is of a crossbar design. Specifically, thedriver interface 182 comprises afirst bar 184 andsecond bar 186 that are orientated perpendicularly to each other. In the embodiment shown, thebars bars insert annular sidewalls bars -
FIG. 12 illustrates an alternative embodiment of adriver interface 188. As shown, thedriver interface 188 comprises a bar and boss interface. Thisdriver interface 188 comprises abar portion 190 extending to aboss 192. Theboss 192 has opposed semi-circular sides meeting thebar portion 190. Similar to the previous crossedbar driver interface 182, the bar andboss interface 188 may extend across the diameter of the base portion of theinsert -
FIGS. 16A and16B illustrate embodiments of the operation of thebone cutters bone cutter insert shell 20. As illustrated inFIGS. 2 ,4A ,14A , and16A , in a preferred embodiment, the retracted position is defined as when the insert tissue cutting surfaces 96, 158 are positioned within the shell interior below the shell opening perimeter. Once positioned within the body, theshell 20 of thebone cutter acetabular roof 28 andacetabular labrum 30. - Once the acetabular roof and labrum have been sufficiently reamed, the
reamer shell 20 is rotated in the opposite direction to thereby anchor the reamer shell within surrounding tissue and/or bone. After theshell 20 is anchored, theinsert tissue cutting teeth shell cutting teeth 46 to extend theinsert cutting teeth reamer shell opening 24. Once extended, theinsert insert cutting teeth
The bone cutter anchors 70 are dislodged from the surrounding bone and tissue and thebone cutter - In a preferred embodiment, the
reamer shell 20, inserts 22, 126,collars band 170 are composed of a biocompatible material. More specifically, at least one of thereamer shell 20, inserts 22, 126,collars band 170 may be composed of a biocompatible polymer, metal or ceramic material. Examples of such polymeric materials include, but are not limited to, acrylonitrile butadiene styrene (ABS), polyacrylamides (PARA), polyetherimide (PEI), and polyetheretherketone (PEEK). In addition, examples of metallic materials include, but are not limited to, stainless steel, titanium, MP35N, and a biocompatible metal. - While the preferred embodiments of the cutting device and methods have been described in reference to the environment in which they were developed, they are merely illustrative of the principles of the inventions. Other embodiments and configurations may be devised without departing from the spirit of the inventions and the scope of the appended claims.
- The invention includes the following numbered recitations 1 to 30:
- 1. An orthopedic bone cutter, comprising:
- a) a cutting shell having a shell sidewall with a curvature that comprises at least a portion of a hemisphere, the cutting shell extending from a lower edge towards an imaginary apex, an opening having an opening perimeter extends through the shell sidewall at the imaginary apex to a cutting shell interior, a rotational axis extends through the imaginary apex, the cutting shell being rotatable about the rotational axis;
- b) a flange having an annular flange sidewall defining a flange opening, the flange extending from the shell opening perimeter at a flange distal end to a flange proximal end positioned within the shell interior;
- c) a plurality of outwardly extending and spaced apart shell cutting teeth;
- d) an insert extending from an insert proximal end to an insert distal end, the insert comprising an annular insert sidewall that meets an insert end wall at the insert distal end, the insert positioned within the flange opening along the rotational axis, wherein the insert distal end faces the imaginary apex;
- e) a plurality of outwardly extending and spaced apart insert cutting teeth; and
- f) wherein the insert is capable of rotational and axial movement about the rotational axis.
- 2. The orthopedic bone cutter of recitation 1, wherein rotation of the insert causes the insert to move axially along the rotational axis either in a distal direction towards the imaginary apex or in a proximal direction within cutting shell interior.
- 3. The orthopedic bone cutter of recitation 1, wherein the shell cutting teeth and the insert cutting teeth are in opposite directions.
- 4. The orthopedic bone cutter of recitation 1, wherein the insert end wall comprises a convex shape that outwardly projects in a distal direction.
- 5. The orthopedic bone cutter of recitation 1, wherein the insert end wall has a curvature extending in a distal direction, wherein the curvature has a radius of curvature that ranges from about 1 cm to about 5 cm originating from within the shell interior.
- 6. The orthopedic bone cutter of recitation 1, further comprising a collar that extends from a collar proximal end to a collar distal end, the collar having an annular collar sidewall with opposed interior and exterior collar sidewall surfaces defining a collar opening, wherein the insert is positioned within the collar opening with the insert distal end facing the apex, and wherein the collar comprises:
- a) at least one slot having spaced apart slot proximal and distal ends, wherein the slot distal end is spaced from the collar distal end, the slot proximal end is spaced from the collar proximal end; and
- b) a groove orientated about perpendicular to the rotational axis formed at least partially within the collar sidewall from the interior surface, wherein the slot distal end meets the groove, and wherein the groove extends circumferentially about the annular collar sidewall at the collar distal end.
- 7. The orthopedic bone cutter of recitation 6, wherein at least one pin extends outwardly from the insert sidewall exterior surface, wherein the at least one pin is received within a respective collar slot and is capable of riding therewithin.
- 8. The orthopedic bone cutter of recitation 1, wherein the reamer shell or insert is composed of a material selected from the group consisting of acrylonitrile butadiene styrene (ABS), polyacrylamides (PARA), polyetherimide (PEI), polyetheretherketone (PEEK), a biocompatible polymeric material, and combinations thereof.
- 9. The orthopedic bone cutter of recitation 1, further comprising a shaft driver interface having a bar and boss configuration or a cross bar configuration positioned at the insert proximal end.
- 10. The orthopedic bone cutter of recitation 1, further comprising a collar that extends from a collar proximal end to a collar distal end having an annular collar sidewall with opposed interior and exterior collar sidewall surfaces defining a collar opening, at least one pin extends from the collar annular sidewall interior surface towards the rotational axis, the collar distal end being secured to the flange proximal end, wherein the insert is positioned within the collar opening, the insert capable of rotational and axial movement therewithin.
- 11. The orthopedic bone cutter of
recitation 10, wherein at least one slot extends at least partially within the insert sidewall from an exterior insert surface, the at least one slot extending from a slot proximal end spaced from the insert proximal end to a slot distal end spaced from the insert distal end, wherein the at least one slot is configured to receive the at least one pin. - 12. The orthopedic bone cutter of
recitation 10, wherein a groove is formed at least partially within the insert sidewall from an exterior insert surface, the groove extending circumferentially about the annular insert sidewall at the insert proximal end, wherein the groove forms a track configured to receive the at least one pin. - 13. The orthopedic bone cutter of
recitation 10, wherein a band comprising an annular band sidewall extending from a band proximal end to a band distal end having opposed interior and exterior sidewall surfaces is positioned at the collar proximal end, wherein the band comprises a lip that extends from the interior sidewall surface towards the rotational axis at the band proximal end. - 14. The orthopedic bone cutter of recitation 1, further comprising an anchor that outwardly extends from an exterior surface of the reamer shell, the anchor having an anchor tissue cutting surface.
- 15. The orthopedic bone cutter of
recitation 14, wherein the anchor tissue cutting surface is oriented in an opposite direction as the shell cutting teeth. - 16. The orthopedic bone cutter of recitation 15, wherein the shell comprises an anchor opening that extends through the shell sidewall at the shell proximal end, wherein at least a portion of the anchor tissue cutting surface extends over the opening.
- 17. An orthopedic bone cutter, comprising:
- a) a cutting shell having a shell sidewall with curvature that comprises at least a portion of a hemisphere, the cutting shell, extending from a lower edge defining a lower perimeter to an intermediate edge defining an intermediate perimeter located on an imaginary intermediate plane that is spaced from and positioned between an imaginary apex and the lower edge, wherein the lower perimeter of the lower edge is greater than the intermediate perimeter of the intermediate edge, the cutting shell being rotatable about a rotational axis;
- b) a flange having an annular flange sidewall that defines a flange opening that extends from a flange distal end at the intermediate edge to a flange proximal end extending towards the shell lower edge;
- c) a plurality of outwardly extending and spaced apart cutting shell teeth;
- d) an insert having an insert proximal end that extends to an insert distal end, wherein the insert comprises an annular insert sidewall wall that meets an insert end wall at the insert distal end, the insert positioned within the flange opening along the rotational axis, wherein the insert distal end faces the imaginary apex;
- e) a plurality of outwardly extending and spaced apart insert cutting teeth; and
- f) wherein the insert is capable of rotational and axial movement about the rotational axis.
- 18. The orthopedic bone cutter of recitation 17, wherein rotation of the insert causes the insert to move axially in distal direction towards the imaginary apex or in a proximal direction towards the shell lower edge.
- 19. The orthopedic bone cutter of recitation 17, wherein the shell cutting teeth and the insert cutting teeth are oriented in opposite directions.
- 20. The orthopedic bone cutter of recitation 17, wherein the insert end wall comprises a convex shape that outwardly projects in a distal direction.
- 21. The orthopedic bone cutter of recitation 17, further comprising a collar that extends from a collar proximal end to a collar distal end, the collar having an annular collar sidewall with opposed interior and exterior collar sidewall surfaces defining a collar opening, wherein the insert is positioned within the collar opening with the insert distal end facing the apex, and wherein the collar comprises:
- a) at least one slot having spaced apart slot proximal and distal ends, wherein the slot distal end is spaced from the collar distal end, the slot proximal end is spaced from the collar proximal end; and
- b) a groove orientated about perpendicular to the rotational axis formed at least partially within the collar sidewall from the interior surface, wherein the slot distal end meets the groove, and wherein the groove extends circumferentially about the annular collar sidewall at the collar distal end.
- 22. The orthopedic bone cutter of recitation 21, wherein a pin extends outwardly from the insert sidewall exterior surface, and wherein the pin is received within the collar slot and is capable of riding therewithin.
- 23. The orthopedic bone cutter of recitation 17, further comprising a shaft driver interface having a bar and boss configuration or a cross bar configuration positioned at the insert proximal end.
- 24. The orthopedic bone cutter of recitation 17, further comprising a collar that extends from a collar proximal end to a collar distal end, the collar comprises an annular collar sidewall having opposed interior and exterior collar sidewall surfaces that defines a collar opening, at least one pin extends from the collar annular sidewall interior surface towards the longitudinal axis, the collar distal end being secured to the flange proximal end, wherein the insert is positioned within the collar opening capable of rotational and axial movement therewithin.
- 25. The orthopedic bone cutter of
recitation 24, wherein at least one slot extends at least partially within the insert sidewall from the exterior sidewall surface, the at least one slot extending from a slot proximal end spaced from the insert proximal end to a slot distal end spaced from the insert distal end, wherein the at least one pin is received within a respective slot. - 26. The orthopedic bone cutter of
recitation 24, wherein a groove is formed at least partially within the insert sidewall from the exterior sidewall surface, the groove extending circumferentially about the annular insert sidewall at the insert proximal end, wherein the groove forms a track configured to receive the at least one pin. - 27. The orthopedic bone cutter of
recitation 24, wherein a band comprising an annular band sidewall extending from a band proximal end to a band distal end having opposed interior and exterior sidewall surfaces is positioned at the collar proximal end, wherein the band comprises a lip that extends from the interior sidewall surface towards the rotational axis at the band proximal end. - 28. The orthopedic bone cutter of recitation 17, further comprising an anchor that outwardly extends from an exterior surface of the reamer shell, the anchor having an anchor tissue cutting surface.
- 29. The orthopedic bone cutter of
recitation 28, wherein the anchor tissue cutting surface is oriented in an opposite direction as the shell cutting teeth. - 30. The orthopedic bone cutter of recitation 29, wherein the shell comprises an anchor opening that extends through the shell sidewall at the shell proximal end, wherein at least a portion of the anchor tissue cutting surface extends over the opening.
Claims (15)
- An orthopedic bone cutter, comprising:a) a cutting shell having a shell sidewall with a curvature that comprises at least a portion of a hemisphere, the cutting shell extending from a lower edge towards an imaginary apex, an opening having an opening perimeter extends through the shell sidewall at the imaginary apex to a cutting shell interior, a rotational axis extends through the imaginary apex, the cutting shell being rotatable about the rotational axis;b) a flange having an annular flange sidewall defining a flange opening, the flange extending from the shell opening perimeter at a flange distal end to a flange proximal end positioned within the shell interior;c) a plurality of outwardly extending and spaced apart shell cutting teeth;d) an insert extending from an insert proximal end to an insert distal end, the insert comprising an annular insert sidewall that meets an insert end wall at the insert distal end, the insert positioned within the flange opening along the rotational axis, wherein the insert distal end faces the imaginary apex;e) a plurality of outwardly extending and spaced apart insert cutting teeth; andf) wherein the insert is capable of rotational and axial movement about the rotational axis.
- The orthopedic bone cutter of claim 1, wherein rotation of the insert causes the insert to move axially along the rotational axis either in a distal direction towards the imaginary apex or in a proximal direction within cutting shell interior.
- The orthopedic bone cutter of claims 1 or 2, wherein the shell cutting teeth and the insert cutting teeth are in opposite directions.
- The orthopedic bone cutter of any of claims 1 to 3, wherein the insert end wall comprises a convex shape that outwardly projects in a distal direction.
- The orthopedic bone cutter of any of claims 1 to 4, wherein the insert end wall has a curvature extending in a distal direction, wherein the curvature has a radius of curvature that ranges from about 1 cm to about 5 cm originating from within the shell interior.
- The orthopedic bone cutter of any of claims 1 to 5, further comprising a collar that extends from a collar proximal end to a collar distal end, the collar having an annular collar sidewall with opposed interior and exterior collar sidewall surfaces defining a collar opening, wherein the insert is positioned within the collar opening with the insert distal end facing the apex, and wherein the collar comprises:a) at least one slot having spaced apart slot proximal and distal ends, wherein the slot distal end is spaced from the collar distal end, the slot proximal end is spaced from the collar proximal end; andb) a groove orientated about perpendicular to the rotational axis formed at least partially within the collar sidewall from the interior surface, wherein the slot distal end meets the groove, and wherein the groove extends circumferentially about the annular collar sidewall at the collar distal end.
- The orthopedic bone cutter of any of claims 1 to 6, wherein at least one pin extends outwardly from the insert sidewall exterior surface, wherein the at least one pin is received within a respective collar slot and is capable of riding therewithin.
- The orthopedic bone cutter of any of claims 1 to 7, further comprising a shaft driver interface having a bar and boss configuration or a cross bar configuration positioned at the insert proximal end.
- The orthopedic bone cutter of any of claims 1 to 8, further comprising a collar that extends from a collar proximal end to a collar distal end having an annular collar sidewall with opposed interior and exterior collar sidewall surfaces defining a collar opening, at least one pin extends from the collar annular sidewall interior surface towards the rotational axis, the collar distal end being secured to the flange proximal end, wherein the insert is positioned within the collar opening, the insert capable of rotational and axial movement therewithin.
- The orthopedic bone cutter of any of claims 1 to 9, wherein at least one slot extends at least partially within the insert sidewall from an exterior insert surface, the at least one slot extending from a slot proximal end spaced from the insert proximal end to a slot distal end spaced from the insert distal end, wherein the at least one slot is configured to receive the at least one pin.
- The orthopedic bone cutter of any of claims 1 to 10, wherein a groove is formed at least partially within the insert sidewall from an exterior insert surface, the groove extending circumferentially about the annular insert sidewall at the insert proximal end, wherein the groove forms a track configured to receive the at least one pin.
- The orthopedic bone cutter of any of claims 1 to 11, wherein a band comprising an annular band sidewall extending from a band proximal end to a band distal end having opposed interior and exterior sidewall surfaces is positioned at the collar proximal end, wherein the band comprises a lip that extends from the interior sidewall surface towards the rotational axis at the band proximal end.
- The orthopedic bone cutter of any of claims 1 to 12, further comprising an anchor that outwardly extends from an exterior surface of the reamer shell, the anchor having an anchor tissue cutting surface.
- The orthopedic bone cutter of any of claims 1 to 13, wherein the anchor tissue cutting surface is oriented in an opposite direction as the shell cutting teeth.
- The orthopedic bone cutter of any of claims 1 to 14, wherein the shell comprises an anchor opening that extends through the shell sidewall at the shell proximal end, wherein at least a portion of the anchor tissue cutting surface extends over the opening.
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US201562266342P | 2015-12-11 | 2015-12-11 |
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EP16203474.8A Active EP3178417B1 (en) | 2015-12-11 | 2016-12-12 | Minimally invasive bone sparing acetabular reamer |
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EP (1) | EP3178417B1 (en) |
Cited By (3)
Publication number | Priority date | Publication date | Assignee | Title |
---|---|---|---|---|
WO2019070580A1 (en) * | 2017-10-04 | 2019-04-11 | Depuy Ireland Unlimited Company | Rotary surgical instrument assembly |
EP3530216A1 (en) * | 2018-02-23 | 2019-08-28 | Hpf S.R.L. | Surgical reamer |
EP3698730A1 (en) * | 2019-02-22 | 2020-08-26 | Hpf S.R.L. | Milling tool for prosthetic surgery operations |
Families Citing this family (2)
Publication number | Priority date | Publication date | Assignee | Title |
---|---|---|---|---|
JP7146694B2 (en) * | 2019-05-22 | 2022-10-04 | 帝人ナカシマメディカル株式会社 | cup reamer |
US11925362B2 (en) * | 2021-12-10 | 2024-03-12 | Depuy Ireland Unlimited Company | Augment reamer and related methods |
Citations (5)
Publication number | Priority date | Publication date | Assignee | Title |
---|---|---|---|---|
US5709688A (en) | 1995-06-07 | 1998-01-20 | Othy, Inc. | Acetabular reamer cup and method of producing the same |
US20080161813A1 (en) * | 2006-12-30 | 2008-07-03 | Precimed S.A. | Cut-off acetabular reamer |
US7608076B2 (en) | 2005-04-29 | 2009-10-27 | Greatbatch Medical S.A. | Minimally invasive collapsible surgical reamer |
US7850692B2 (en) | 2002-04-12 | 2010-12-14 | Greatbatch Medical S.A. | Minimally invasive surgical reamer and connection |
US20140271005A1 (en) * | 2013-03-16 | 2014-09-18 | Ping Xie | Methods and apparatus for preparing a hemispherical surface |
Family Cites Families (13)
Publication number | Priority date | Publication date | Assignee | Title |
---|---|---|---|---|
FR2755603B1 (en) * | 1996-11-12 | 1999-02-26 | Jacques Preaut | ASSEMBLY OF ANCILLARS FOR LAYING HIP PROSTHESIS COTYLS, AND READY-TO-FIT COTYL PROSTHETIC ASSEMBLY |
US7632276B2 (en) | 2004-07-29 | 2009-12-15 | Greatbatch Medical Sa | Minimally invasive collapsible surgical reamer |
US7513899B2 (en) | 2006-01-27 | 2009-04-07 | Howmedica Osteonics Corp. | Acetabular reamer connection mechanism |
US20070276396A1 (en) * | 2006-05-10 | 2007-11-29 | Howmedica Osteonics Corp. | Modular acetabular reamer |
US20090088757A1 (en) * | 2007-10-02 | 2009-04-02 | Howmedica Osteonics Corp. | Acetabular reamer |
US8679124B2 (en) * | 2007-12-20 | 2014-03-25 | Greatbatch Medical S.A. | Disposable acetabular reamer from flat stock |
EP2359755B1 (en) * | 2010-02-12 | 2014-01-15 | Greatbatch Ltd. | Disposable reamer |
IT1401236B1 (en) * | 2010-07-26 | 2013-07-12 | Hpf S R L Ora Hpf S P A | MILLING TOOL FOR PROSTHETIC SURGERY OPERATIONS |
EP3318202B1 (en) * | 2011-01-21 | 2024-02-21 | Greatbatch Ltd. | Disposable surgical hemispherical cutter for convex surfaces |
US8961520B2 (en) * | 2011-11-28 | 2015-02-24 | Christopher G. Sidebotham | Medical cutting tool quality control systems and methods |
US10543003B2 (en) * | 2014-09-30 | 2020-01-28 | Depuy Ireland Unlimited Company | Orthopaedic surgical instrument assembly and method of manufacturing same |
US10092304B2 (en) * | 2014-09-30 | 2018-10-09 | Depuy Ireland Unlimited Company | Orthopaedic surgical instrument assembly for reaming a patient's acetabulum |
US9675364B2 (en) * | 2014-09-30 | 2017-06-13 | Depuy Ireland Unlimited Company | Grater and trial liner |
-
2016
- 2016-12-12 EP EP16203474.8A patent/EP3178417B1/en active Active
- 2016-12-12 US US15/375,699 patent/US10478197B2/en active Active
Patent Citations (6)
Publication number | Priority date | Publication date | Assignee | Title |
---|---|---|---|---|
US5709688A (en) | 1995-06-07 | 1998-01-20 | Othy, Inc. | Acetabular reamer cup and method of producing the same |
US7850692B2 (en) | 2002-04-12 | 2010-12-14 | Greatbatch Medical S.A. | Minimally invasive surgical reamer and connection |
US7608076B2 (en) | 2005-04-29 | 2009-10-27 | Greatbatch Medical S.A. | Minimally invasive collapsible surgical reamer |
US20080161813A1 (en) * | 2006-12-30 | 2008-07-03 | Precimed S.A. | Cut-off acetabular reamer |
US8052689B2 (en) | 2006-12-30 | 2011-11-08 | Greatbatch Medical S.A. | Cut-off acetabular reamer |
US20140271005A1 (en) * | 2013-03-16 | 2014-09-18 | Ping Xie | Methods and apparatus for preparing a hemispherical surface |
Non-Patent Citations (1)
Title |
---|
K DE SMET ET AL.: "The hip resurfacing handbook: A practical guide to the use and management of modern hip resurfacings", 2013, pages: 326 |
Cited By (6)
Publication number | Priority date | Publication date | Assignee | Title |
---|---|---|---|---|
WO2019070580A1 (en) * | 2017-10-04 | 2019-04-11 | Depuy Ireland Unlimited Company | Rotary surgical instrument assembly |
CN111542278A (en) * | 2017-10-04 | 2020-08-14 | 德普伊爱尔兰无限公司 | Rotary surgical instrument assembly |
US11504138B2 (en) | 2017-10-04 | 2022-11-22 | Depuy Ireland Unlimited Company | Rotary surgical instrument assembly |
CN111542278B (en) * | 2017-10-04 | 2023-10-27 | 德普伊爱尔兰无限公司 | Rotary surgical instrument assembly |
EP3530216A1 (en) * | 2018-02-23 | 2019-08-28 | Hpf S.R.L. | Surgical reamer |
EP3698730A1 (en) * | 2019-02-22 | 2020-08-26 | Hpf S.R.L. | Milling tool for prosthetic surgery operations |
Also Published As
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EP3178417B1 (en) | 2019-09-25 |
US20170164955A1 (en) | 2017-06-15 |
US10478197B2 (en) | 2019-11-19 |
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